WO2013034709A1 - Dosimétrie de rayonnement in situ non invasive - Google Patents

Dosimétrie de rayonnement in situ non invasive Download PDF

Info

Publication number
WO2013034709A1
WO2013034709A1 PCT/EP2012/067539 EP2012067539W WO2013034709A1 WO 2013034709 A1 WO2013034709 A1 WO 2013034709A1 EP 2012067539 W EP2012067539 W EP 2012067539W WO 2013034709 A1 WO2013034709 A1 WO 2013034709A1
Authority
WO
WIPO (PCT)
Prior art keywords
gas
volume
dose
substance
filled microparticles
Prior art date
Application number
PCT/EP2012/067539
Other languages
English (en)
Inventor
Jan D'HOOGE
Helge Pfeiffer
Koen VAN DEN ABEELE
Erik VERBOVEN
Emiliano D'AGOSTINO
Original Assignee
Katholieke Universiteit Leuven
Sck•Cen
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Katholieke Universiteit Leuven, Sck•Cen filed Critical Katholieke Universiteit Leuven
Priority to US14/343,112 priority Critical patent/US9035268B2/en
Priority to EP12756201.5A priority patent/EP2758130B1/fr
Publication of WO2013034709A1 publication Critical patent/WO2013034709A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1048—Monitoring, verifying, controlling systems and methods
    • A61N5/1071—Monitoring, verifying, controlling systems and methods for verifying the dose delivered by the treatment plan
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/481—Diagnostic techniques involving the use of contrast agent, e.g. microbubbles introduced into the bloodstream
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/02—Dosimeters
    • G01T1/023—Scintillation dose-rate meters
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/20—Measuring radiation intensity with scintillation detectors
    • G01T1/2012—Measuring radiation intensity with scintillation detectors using stimulable phosphors, e.g. stimulable phosphor sheets
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A61B8/0833—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00—Preparations for testing in vivo
    • A61K49/22—Echographic preparations; Ultrasound imaging preparations ; Optoacoustic imaging preparations
    • A61K49/222—Echographic preparations; Ultrasound imaging preparations ; Optoacoustic imaging preparations characterised by a special physical form, e.g. emulsions, liposomes
    • A61K49/223—Microbubbles, hollow microspheres, free gas bubbles, gas microspheres
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/10—Dispersions; Emulsions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/48—Preparations in capsules, e.g. of gelatin, of chocolate
    • A61K9/50—Microcapsules having a gas, liquid or semi-solid filling; Solid microparticles or pellets surrounded by a distinct coating layer, e.g. coated microspheres, coated drug crystals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/48—Preparations in capsules, e.g. of gelatin, of chocolate
    • A61K9/50—Microcapsules having a gas, liquid or semi-solid filling; Solid microparticles or pellets surrounded by a distinct coating layer, e.g. coated microspheres, coated drug crystals
    • A61K9/51—Nanocapsules; Nanoparticles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy

Definitions

  • the invention relates to the field of radiation dosimetry. More specifically it relates to systems and methods for in-situ radiation dosimetry, in particular non-invasive radiation dosimetry.
  • US2011/121188 discloses a system which comprises internally positioning single-use MOSFET dosimeters in a patient's body to evaluate the radiation dose delivered during a medical procedure or treatment session
  • US2004/236207 discloses positioning single-use adhesive dosimeter patches just onto the skin of a patient. Therefore, the dosage of energy that is planned for, often cannot be measured, determined or monitored very accurately, in the tumor itself.
  • the present invention provides systems for measuring radiation dose.
  • the system comprises an excitation device adapted for directing an energy wave at a volume of a substance comprising gas-filled microparticles, a detector for detecting a response signal emitted and/or modified from the volume of the substance comprising gas-filled microparticles, and a control unit, wherein the control unit is adapted for calculating a dose of ionizing radiation previously or simultaneously received by the volume of the substance based on the response signal.
  • the gas-filled microparticles may be elastic.
  • the control unit may be adapted for calculating a dose of ionizing radiation received by the volume of the substance, taking into account a measured or detected change of elasticity of the gas-filled microparticles.
  • the microparticles may comprise a Young modulus in the range of 0 to 30 GPa, 0 not included, more specifically in the range of 0 to 15 GPa, 0 not included, for example in the range of 0.01 to 15 GPa.
  • the gas-filled microparticles may be echogenic.
  • the gas-filled microparticles may be encapsulated.
  • the gas-filled microparticles may be adapted to comprise at least a binding site.
  • the gas-filled microparticles may be under suspension.
  • the excitation device comprises an ultrasound or electromagnetic ( F) transducer and the detector is adapted for acquiring an ultrasonic or electromagnetic (RF) response signal from the volume of the substance comprising encapsulated gas-filled microparticles.
  • F ultrasound or electromagnetic
  • RF ultrasonic or electromagnetic
  • the gas-filled microparticles remain intact when receiving a dose of ionizing radiation. They may be destroyed thereafter, for releasing their content.
  • a pressure or energy higher than 60 kPa may be used to obtain the destruction of the microparticles, for example an energy burst of up to 1000 kPa.
  • control unit is furthermore adapted for determining a spatial distribution, e.g. a planar and/or a volumetric distribution, of the received dose of ionizing radiation.
  • control unit is adapted for calculating, during radiotherapy, a dose of ionizing radiation received by said volume of the substance.
  • control unit is adapted for calculating, during radiotherapy, a dose of ionizing radiation received by a patient having said volume of the substance administered.
  • the volume of the substance comprising the encapsulated gas-filled microparticles is dispersible.
  • the encapsulated gas- filled microparticles are encapsulated gas-filled microspheres.
  • the volume of a substance comprising the gas-filled microparticles, for example encapsulated is biocompatible.
  • the volume of the substance comprising encapsulated gas-filled microparticles is adapted to dissolve, for example after a time in order of minutes. In some embodiments of the invention, the volume of the substance comprising encapsulated gas-filled microparticles is adapted to interact with the dose of ionizing radiation received by said volume of the substance.
  • the interaction with the dose of ionizing radiation results in a change of physical properties or chemical properties or a combination of physical and chemical properties of the gas-filled microparticles, whereby said change can be irreversible.
  • the control unit may be adapted for calculating a dose of ionizing radiation received by the volume of the substance, taking into account a change of physical properties or chemical properties or a combination of physical and chemical properties of the gas-filled microparticles due to interaction with the dose of ionizing radiation.
  • the physical properties of said encapsulated gas-filled microparticles may comprise one or more properties selected from the group consisting of radius, size distribution, number of particles, shell thickness, shear modulus, shear viscosity, and surface tension.
  • the chemical properties of said encapsulated gas-filled microparticles may comprise one or more properties selected from the group consisting of equilibrium gas pressure, polytrophic gas constant, coefficient of diffusivity in water, permeability through encapsulation, and Ostwald coefficient.
  • the gas-filled microparticles are functionalized.
  • the functionalized gas-filled microparticles are chemically bond with a target having a structural integrity. More specifically, the target may be a specific membrane receptor in a biological cellular matrix.
  • the gas-filled microparticles are composed of a shell and a gas core, wherein the shell is formed by a material selected from the group consisting of albumin, galactose, lipid, polymer and combinations thereof; and the gas core is formed by any of air, octafluoropropane, perfluorocarbon, sulfur hexafluoride, or nitrogen.
  • the encapsulated gas-filled microparticles remain intact when calculating a dose of ionizing radiation.
  • the excitation device may be adapted for keeping the encapsulated gas-filled microparticles intact when directing the energy wave at the volume of the substance comprising the gas-filled microparticles.
  • the energy of the energy wave directed to the volume by the excitation device may be limited to below a predetermined threshold, the predetermined threshold being such that energies below this threshold do not burst or otherwise destroy the gas-filled microparticles.
  • the encapsulated gas-filled microparticles further comprise a pharmacon.
  • the encapsulated gas-filled microparticles after measuring a dose of ionizing radiation received by the volume comprising the encapsulated gas-filled microparticles, are allowed to burst and deliver the pharmacon.
  • a sufficiently high energy burst may be provided to the gas-filled microparticles, for example an energy burst higher than 60 kPa, even up to 1 MPa.
  • gas-filled microparticles are nonradioactive and/or non-luminescent.
  • Embodiments of the invention provide that the dose of ionizing radiation applied to a patient is smaller than 300 Gy, more specifically smaller than 100 Gy.
  • the volume of the substance comprising gas-filled microparticles is a medical agent. More specifically said medical agent is preferably selected from a group consisting of contrast agents and therapeutic agents.
  • control unit is adapted for controlling the set-up and parameters of the detector, e.g. amplitude, frequency and/or waveform.
  • the present invention provides methods for measuring a received dose of ionizing radiation.
  • the method comprises directing an energy wave at a volume of a substance comprising gas-filled microparticles, whereby said volume of the substance has been previously exposed to ionizing radiation, detecting a response signal from the volume and determining the radiation dose received by the volume during the previously applied ionizing radiation exposure, taking into account the detected response signal.
  • detecting a response signal comprises detecting an interaction between the previously applied ionizing radiation and said volume of the substance.
  • the method further comprises quantifying said detected interaction by analyzing a dispersive response of the volume in function of the received dose of ionizing radiation.
  • analyzing the dispersive response comprises analyzing dispersive characteristics of parameters of said encapsulated gas-filled microparticles in function of the dose of ionizing radiation.
  • said parameters comprise one or more parameters selected from the group consisting of phase velocity, attenuation and nonlinearity.
  • the method furthermore includes a time correcting method, the time correcting method comprising directing an energy wave at a volume of the substance comprising functionalized gas-filled microparticles, whereby said volume is not exposed to ionizing radiation; detecting a response signal from the volume; determining a time correction value taking into account said detected response signal; and applying said time correction value to a detected response signal, determined on a volume previously exposed to ionizing radiation.
  • a time correcting method comprising directing an energy wave at a volume of the substance comprising functionalized gas-filled microparticles, whereby said volume is not exposed to ionizing radiation; detecting a response signal from the volume; determining a time correction value taking into account said detected response signal; and applying said time correction value to a detected response signal, determined on a volume previously exposed to ionizing radiation.
  • Preferably directing an energy wave at the volume of the substance comprises emitting an ultrasonic or F wave and detecting a response signal comprises detecting an ultrasonic or RF response signal.
  • determining the radiation dose includes determining a spatial distribution, e.g. a planar and/or a volumetric distribution, of the radiation dose.
  • the method furthermore comprises determining, during and/or after radiotherapy, the radiation dose received by said volume of the substance.
  • real-time determination of received radiation doses may be performed, i.e. during application of the radiation dose.
  • the method furthermore comprises determining, during and/or after radiotherapy, the radiation dose received by a patient having said volume of the substance administered.
  • the method is non-invasive. No surgical steps need to be performed to get a radiation dose detector in a patient at the level of the site to be irradiated.
  • the present invention provides the use of a volume of a substance for dosimetry, said volume comprising gas-filled microparticles.
  • the gas-filled microparticles may be encapsulated.
  • the gas-filled microparticles are functionalized.
  • the gas-filled microparticles may be chemically bond with a target having structural integrity.
  • the target may for example be a specific membrane receptor in a biological cellular matrix.
  • the volume of the substance may be a medical agent.
  • the medical agent is selected from a group consisting of contrast agents and therapeutic agents.
  • the gas-filled microparticles may be composed of a shell and a gas core.
  • the shell may for example be formed by a material selected from the group consisting of albumin, galactose, lipid, polymer and combinations thereof.
  • the gas core may for example be formed by any of air, octafluoropropane, perfluorocarbon, sulfur hexafluoride or nitrogen.
  • the gas-filled microparticles may be composed of a gas core encapsulated by a lipid monolayer membrane shell.
  • the gas comprises air, perfluorocarbon and/or nitrogen.
  • the gas-filled microparticles are elastic.
  • the gas-filled microparticles may comprise a Young's modulus in the range of 0 to 30 GPa, 0 not included, more specifically in the range of 0 to 15 GPa, 0 not included, for example in the range of 0.01 to 15 GPa.
  • the volume is adapted to be used for in-situ dosimetry and/or to monitor a radiation dose applied to a patient.
  • said monitoring is performed in real-time and/or said monitoring is non-invasive.
  • the gas-filled microparticles may be echogenic.
  • the gas-filled microparticles may be adapted to comprise at least a binding site.
  • the gas-filled microparticles may be under suspension. In a use according to embodiments of the present invention, the gas-filled microparticles may be adapted to remain intact when receiving and/or calculating a dose of ionizing radiation.
  • said volume of the substance comprising encapsulated gas-filled microparticles may be dispersible.
  • said encapsulated gas- filled microparticles may be encapsulated gas-filled microspheres.
  • the volume of the substance comprising encapsulated gas-filled microparticles may be biocompatible.
  • said volume of the substance comprising encapsulated gas-filled microparticles may be adapted to dissolve after a time in order of minutes.
  • said volume of the substance comprising encapsulated gas-filled microparticles may be adapted to interact with the dose of ionizing radiation received by said volume of the substance. Said interaction with the dose of ionizing radiation may result in a change of physical properties or chemical properties or a combination of physical and chemical properties of the gas-filled microparticles.
  • the physical properties of said encapsulated gas-filled microparticles may comprise one or more properties selected from the group consisting of radius, size distribution, number of particles, shell thickness, shear modulus, shear viscosity, and surface tension.
  • the chemical properties of said encapsulated gas-filled microparticles may comprise one or more properties selected from the group consisting of equilibrium gas pressure, polytrophic gas constant, coefficient of diffusivity in water, permeability through encapsulation, and Ostwald coefficient.
  • the encapsulated gas- filled microparticles may further comprise a pharmacon.
  • the encapsulated gas-filled microparticles may be adapted to burst and deliver the pharmacon after measuring a dose of ionizing radiation received by the volume comprising the encapsulated gas-filled microparticles.
  • the gas-filled microparticles may be non-radioactive. In a use according to embodiments of the present invention, the gas-filled microparticles may be non-luminescent.
  • the present invention provides a system for measuring radiation dose.
  • the system comprises an excitation device adapted for directing an energy wave at a contrast agent which comprises dispersed gas-filled microparticles.
  • the system further comprises a detector for detecting a response signal emitted from the contrast agent and a control unit.
  • This control unit is adapted for calculating, based on the response signal, a dose of ionizing radiation previously received by the contrast agent.
  • the control unit may be adapted for controlling an experimental set-up and parameters of a read-out device, such as for example amplitude, frequency and/or waveform.
  • the excitation device may comprise a dedicated wave source, e.g. a mechanical or electromagnetic wave source, such as for example an ultrasound transducer or electromagnetic (radio-frequency- F) emitter, and the detector may be adapted for acquiring a response signal, e.g. a mechanical or electromagnetic response signal, such as for example an ultrasonic or electromagnetic (RF) response signal, from the contrast agent.
  • a dedicated wave source e.g. a mechanical or electromagnetic wave source, such as for example an ultrasound transducer or electromagnetic (radio-frequency- F) emitter
  • the detector may be adapted for acquiring a response signal, e.g. a mechanical or electromagnetic response signal, such as for example an ultrasonic or electromagnetic (RF) response signal, from the contrast agent.
  • a response signal e.g. a mechanical or electromagnetic response signal, such as for example an ultrasonic or electromagnetic (RF) response signal
  • control unit may furthermore be adapted for determining a spatial distribution, e.g. a planar and/or a volumetric distribution, of the received dose of ionizing radiation.
  • control unit may be furthermore adapted for calculating, during radiotherapy, a dose of ionizing radiation received by a patient having said contrast agent administered.
  • the present invention provides a method for measuring a received dose of ionizing radiation.
  • the method comprises directing an energy wave at a contrast agent comprising dispersed gas-filled microparticles and previously exposed to ionizing radiation; and detecting a response signal from the contrast agent.
  • the method further comprises determining the radiation dose received by the contrast agent during the ionizing radiation exposure, taking into account the detected response signal.
  • directing an energy wave may comprise emitting an ultrasonic or electromagnetic (RF) wave and detecting a response signal may comprise detecting an ultrasonic or electromagnetic (RF) response signal.
  • RF ultrasonic or electromagnetic
  • determining the radiation dose may include determining a spatial distribution, e.g. a planar and/or a volumetric distribution, of the radiation dose.
  • a method according to embodiments of the present invention may furthermore comprise determining, during radiotherapy, the radiation dose received by a patient having said contrast agent administered.
  • the present invention provides the use of a contrast agent for non- invasive in-situ dosimetry.
  • the contrast agent may comprise dispersed gas-filled micro-bubbles.
  • the gas-filled micro- bubbles may be composed of a gas core encapsulated by a lipid monolayer membrane shell.
  • the gas may comprise air, perfluorocarbon and/or nitrogen.
  • the gas may also comprise a mixture of gasses.
  • the present invention provides a computer program product for, if implemented on a control unit, performing a method according to the second or fifth aspect of the present invention.
  • the present invention provides a data carrier storing a computer program product according to the seventh aspect of the present invention.
  • data carrier is equal to the terms “carrier medium” or "computer readable medium”, and refers to any medium that participates in providing instructions to a processor for execution.
  • Such a medium may take many forms, including but not limited to, non-volatile media, volatile media, and transmission media.
  • Non-volatile media include, for example, optical or magnetic disks, such as a storage device which is part of mass storage.
  • Volatile media include dynamic memory such as RAM.
  • Common forms of computer readable media include, for example, a floppy disk, a flexible disk, a hard disk, magnetic tape, or any other magnetic medium, a CD- ROM, any other optical medium, punch cards, paper tapes, any other physical medium with patterns of holes, a RAM, a PROM, an EPROM, a FLASH-EPROM, any other memory chip or cartridge, a carrier wave as described hereafter, or any other medium from which a computer can read.
  • Various forms of computer readable media may be involved in carrying one or more sequences of one or more instructions to a processor for execution.
  • the instructions may initially be carried on a magnetic disk of a remote computer.
  • the remote computer can load the instructions into its dynamic memory and send the instructions over a telephone line using a modem.
  • a modem local to the computer system can receive the data on the telephone line and use an infrared transmitter to convert the data to an infrared signal.
  • An infrared detector coupled to a bus can receive the data carried in the infra-red signal and place the data on the bus.
  • the bus carries data to main memory, from which a processor retrieves and executes the instructions.
  • the instructions received by main memory may optionally be stored on a storage device either before or after execution by a processor.
  • the instructions can also be transmitted via a carrier wave in a network, such as a LAN, a WAN or the internet.
  • Transmission media can take the form of acoustic or light waves, such as those generated during radio wave and infrared data communications. Transmission media include coaxial cables, copper wire and fibre optics, including the wires that form a bus within a computer.
  • the present invention provides in transmission of a computer program product according to the seventh aspect of the present invention over a network.
  • different gas-filled micro- or nanoparticles or bubbles which are preferably biocompatible, can be used to perform in-situ dosimetry in a non-invasive way.
  • the effect of radiation on the particles can additionally be characterized in different radiation fields, going from calibration sources, up to clinical photon and particle fields.
  • Micro- or nanoparticles or bubbles according to embodiments of the invention may be adapted for injection into living bodies, e.g. for the purpose of ultrasonic echography.
  • Embodiments of the present invention provide a medium, preferably comprising gas- filled micro- or nanoparticles, for injection into living bodies, e.g. for the purpose of ultrasonic echography and, more particularly, injectable liquid compositions comprising microbubbles of air or physiologically acceptable gases as stable dispersions or suspensions in an aqueous liquid carrier.
  • These compositions may be used as contrast agents in ultrasonic echography to image the inside of blood-stream vessels and other cavities of living beings, e.g. human patients and animals.
  • Other uses, however, are also contemplated as disclosed hereafter.
  • Embodiments of the invention can also comprise dry compositions which, upon admixing with an aqueous carrier liquid, will preferably generate the foregoing sterile suspension of microbubbles thereafter usable as contrast agent for ultrasonic echography and other purposes.
  • microbodies like microspheres or microglobules of air or a gas, e.g. microbubbles or micro-balloons, suspended in a liquid are exceptionally efficient ultrasound reflectors for echography.
  • micro- or nanobubble specifically designates air or gas globules in suspension in a liquid which generally results from the introduction therein of air or a gas in divided form, the liquid preferably also containing surfactants or tensides to control the surface properties thereof and the stability of the bubbles.
  • the internal volume of the microbubbles is limited by the gas/liquid interface, or in other words, the microbubbles according to embodiments of the invention are only bounded by a rather evanescent envelope involving the molecules of the liquid and surfactant loosely bound at the gas to liquid junction boundary.
  • bubbles according to embodiments of the invention versus the microcapsules of the prior art surrounded by a rigid but breakable membrane, like for instance glass, which may irreversibly fracture under stress is that when the present suspensions are subject to sudden pressure changes, the present bubbles will momentarily contract elastically and then resume their original shape when the pressure is released. This is important in clinical practice when the microbubbles are for instance pumped through the heart and therefore are exposed to alternating pressure pulses.
  • the bubble suspensions of the present invention are also useful in other medical/diagnostic applications where it is desirable to target the stabilized microbubbles to specific sites in the body following their injection, for instance to thrombi present in blood vessels, to atherosclerotic lesions (plaques) in arteries, to tumor cells, as well as for the diagnosis of altered surfaces of body cavities, e.g. ulceration sites in the stomach or tumors of the bladder.
  • monoclonal antibodies tailored by genetic engineering, antibody fragments or polypeptides designed to mimic antibodies, bioadhesive polymers, lectins and other site-recognizing molecules to the surfactant layer stabilizing the microbubbles.
  • radiation dose received by a patient may be quantified. It is an advantage of embodiments according to the present invention that radiation dose received by a patient in a predetermined volume of interest, e.g. a tumor site, may be quantified. In addition, it is advantage of embodiments according to the present invention that a homogeneous tumor radiation may be achieved, whereby radiotherapy may be applied in a focused way and whereby an adaptive radiation planning can be enabled.
  • a change of material properties of a volume of a substance e.g. a contrast agent, comprising microspheres, the change of material properties being induced by an interaction between said microspheres and ionizing radiation, may be detected.
  • the contrast agent comprising said micro- or nanospheres
  • no radioactive sources or active sources like f.i. fluorescent sources or fluorescent probes, need to be introduced or administered in a patient.
  • the encapsulated gas-filled micro- or nanoparticles according to embodiments of the present invention are not radioactive nor luminescently active, like for instance fluorescent contrast agents.
  • an exact quantification of the radiation dose to the tumor can be determined by embodiments of the present invention, avoiding not only over- but also under-dosage.
  • Over-dosage implies higher dose to healthy tissues as well; under-dosage corresponds to sub-optimal tumor irradiation that can result, after months or years, in tumor recurrence.
  • embodiments of the present invention improve patient safety. Due to the real-time nature of the technology, treatment errors can be detected and corrected as necessary. This will avoid erroneous irradiations due to mishandling and/or incorrect calibrations. In some embodiments, therapy success can be monitored in a real time fashion without the need of an external imaging system to visualize the tumor.
  • microbubbles can generate such strong signal modifications when applying ultra sound according to embodiments of the invention, a lower intravenous dosage of the volume of the substance comprising dispersed gas-filled microparticles may be needed; micrograms of microbubbles may be sufficient, compared to milligrams for other molecular imaging modalities such as MRI contrast agents.
  • targeting strategies for microbubbles are versatile and modular. Targeting a new area only entails conjugating a new ligand.
  • the gas cores of the microparticles can be composed of air, or heavy gases like perfluorocarbon, or nitrogen.
  • heavy gases are less water-soluble so they are less likely to leak out from the microbubbles to impair echogenicity. Therefore, microbubbles with heavy gas cores according to embodiments of the present invention are likely to last longer in circulation. It is a further advantage that embodiments of the present invention provide devices and methods for assessing doses to any tissue, including not only tumor tissue but also tissues surrounding a tumor.
  • the invention according to some embodiments also provides for dosimetry images for later patient follow-up and/or epidemiological studies.
  • Embodiments of the invention advantageously also provide a method for assessing the treatment of other pathological conditions unrelated to oncology for which radiation therapy is employed.
  • embodiments of the present invention can advantageously also be employed to asses radiation doses in vitro to tissue samples such as biopsies.
  • in situ refers to examining a phenomenon exactly at the place where it occurs (i.e. without moving it to some special medium).
  • in vitro refers to using components of an organism that have been isolated from their usual biological context in order to permit a more detailed or more convenient analysis than can be done with whole organisms.
  • input and generated (output) samples can be processed (or generated) continuously in the time it takes to input and output the same set of samples, independent of the processing delay.
  • tissue as used herein is generic and includes tissues comprising organs and surrounding cell groupings.
  • the term "elastic” as used herein refers to a physical property of a material, whereby the material returns to its original shape after stress is caused. More specifically the term refers to materials with a Young's or E-modulus between 0 and 30 GPa, 0 not being included, more specifically between 0 and 15 GPa, 0 not being included.
  • echo refers to the ability to bounce an echo, e.g. return a signal in ultrasound examinations.
  • an ultrasound signal is used with encapsulated gas-filled microparticles the signal can be increased. This is because microparticles such as microbubbles have a high degree of echogenicity.
  • gas bubbles When gas bubbles are caught in an ultrasonic frequency field, they compress, oscillate, and reflect a characteristic echo- this generates the strong and unique sonogram in contrast-enhanced ultrasound.
  • FIG. 1 shows a schematic overview of a system according to embodiments of a first aspect of the present invention.
  • FIG. 2 shows a schematic overview of a system according to an exemplary embodiment of the first aspect of the present invention, using ultrasonic wave emission and detection as a particular example of an energy wave and response signal.
  • FIG. 3 illustrates how ionizing radiation can interact either with the shell or with the gas core of microbubbles, inducing a change in membrane rigidity and/or curvature of a contrast agent, e.g. an ultrasound contrast agent.
  • a contrast agent e.g. an ultrasound contrast agent.
  • FIG. 4 shows graphs of the time-induced drop of typical dispersion characteristics for the exemplary embodiment using ultrasonic wave emission and detection: (a) phase velocity jump at resonance, (b) attenuation at resonance, and (c) maximum nonlinearity, for non- irradiated micro-bubbles.
  • FIG. 5 shows time-corrected graphs of typical dispersion characteristics for the exemplary embodiment using ultrasonic wave emission and detection: (a) phase velocity jump, (b) maximal attenuation and (c) maximal nonlinearity versus absorbed dose, normalized with respect to non-irradiated bubbles (0 Gy).
  • FIG. 6 shows a graph of the spectral output of a 10 MHz transducer at lOmV input (before amplification) measured by a hydrophone with pre-amplification.
  • FIG. 7 shows the size distribution of MicroMarker microbubbles as determined by analyzing microscopic images.
  • FIG. 8 shows a phase velocity measurement result for pure Isoton II (no dispersion).
  • FIG. 9 shows phase velocity dispersion for a MicroMarker solution containing 4 million microbubbles/ml at two different input amplitudes: 10 mV (solid) and 50 mV (dashed).
  • FIG. 10 shows phase velocity dispersion for a SonoVue contrast solution with a volume fraction of 4x10 s .
  • FIG. 11 shows an attenuation measurement result for Isoton II referenced to distilled water (almost no dispersion).
  • FIG. 12 shows attenuation dispersion for a MicroMarker solution containing 4 million microbubbles/ml at an input voltage of 10 mV.
  • FIG. 13 shows attenuation dispersion for a SonoVue contrast solution with a volume fraction of 4x10 s .
  • FIG. 14 shows the experimental dispersion results for the nonlinearity parameter (a) for Isoton II solution (Blackman-Nuttall window - almost no dispersion), and (b) the influence of different window functions on the appearance of the nonlinearity parameter dispersion for a MicroMarker solution containing 4 million bubbles/ml: Blackman-Nuttall (solid line), Cosine tapered (dashed line) and Hanning (dotted line).
  • FIG. 15 shows the experimental dispersion results for the nonlinearity parameter for a MicroMarker solution containing 4 million microbubbles/ml.
  • FIG. 16 shows the experimental dispersion results for the nonlinearity parameter for a SonoVue contrast solution with a volume fraction of 4x10 s .
  • FIG. 17 shows phase velocity dispersion measurements (a) and attenuation dispersion measurements (b) for different concentrations of a MicroMarker solution ranging from 2 to 8 million bubbles/ml.
  • FIG. 18 shows the shift in resonance frequency as a function of the microbubble concentration for a MicroMarker solution.
  • FIG. 19 shows phase velocity dispersion measurements (a) and attenuation dispersion measurements (b) for different concentrations of a SonoVue contrast solution, ranging from 2xl0 "5 to 8x10 s volume fraction.
  • FIG. 20 shows the shift in the resonance frequency as a function of the microbubble concentration for a SonoVue contrast solution.
  • FIG. 21 shows a plot of a normalized discrete experimental size distribution that was interpolated with the function interpl in Matlab according to a shape-preserving piecewise cubic interpolation.
  • FIG. 22 shows a plot of 5 different Gaussian functions (dash-dotted line) that were used to approximate the experimental size distributions, the resulting sum (solid line) provides a good approximation of the actual curve.
  • FIG. 23 shows a plot of the experimentally achieved phase velocity, attenuation and nonlinearity parameter (circles) dispersions versus the numerically determined dispersions calculated with Hoff's model by insertion of fitted parameters (solid line).
  • FIGS. 24 (a)-(e) illustrate several embodiments of microbubbles which may be used in embodiments of the present invention, and how such microbubbles can transport drugs.
  • first, second and the like in the description and in the claims are used for distinguishing between similar elements and not necessarily for describing a sequence, either temporally, spatially, in ranking or in any other manner. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other sequences than described or illustrated herein. Moreover, the terms top, under and the like in the description and the claims are used for descriptive purposes and not necessarily for describing relative positions. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other orientations than described or illustrated herein.
  • dosimetry relates to determination of an amount of received radiation, e.g. radiation energy, more particularly received ionizing radiation, e.g. radiation energy.
  • ionizing radiation is restricted to radiation capable of ionization in a human or animal body, comprising charged particles such as electrons, protons, pions, nuclei, etc. and/or uncharged particles such as neutrons and photons in the X- and ⁇ -ray energy range.
  • Further derived quantities which may be provided by a system according to the first aspect of the present invention may be the dose rate D , which is the time derivative of the absorbed dose, and/or Kerma K , which is the kinetic energy transferred by uncharged particles to charged particles that are released by them.
  • a common quantity is for example air-Kerma or Kerma in air, i.e. such kinetic energy released in a volume element of air.
  • protection dose quantities try to fill in the blanks by taking into account the detriment on healthy organs or tissue types. The condition that one puts on these dose quantities is that they are practical and reliable. This implies that complex relationships between radiation and risks are strongly simplified.
  • Two important protection dose quantities are the equivalent dose and the effective dose.
  • the equivalent dose H measures the biological effect of an absorbed dose on one organ or tissue type and is the result of a multiplication of the absorbed dose D with a radiation weighting factor (radiation quality factor) w R so that
  • the radiation weighting factor takes into account the fact that the biological effect is dependent on the radiation type, for example: alpha radiation is 20 times more damaging than photon radiation.
  • the present invention relates in a first aspect to a system 1 for measuring radiation dose.
  • a volume of a substance e.g. a contrast agent 2, comprising dispersed gas-filled microparticles 3, e.g. microspheres
  • This exposure of the volume of the substance is performed before performing a measurement method for determining a received radiation does according to embodiments of the present invention.
  • the act of exposing the volume of the substance comprising the dispersed gas-filled microparticles 3 does not form part of any of the embodiments of the present invention.
  • a contrast agent As an example for the volume of the substance, reference is made to a contrast agent. This, however, is not intended to be limiting, and where "contrast agent" is written, the broader terminology "volume of a substance” should be understood.
  • the read-out device of the system analyzes particular characteristics of the contrast agents solution which can be used to infer the radiation dose.
  • Systems 1 according to embodiments of the first aspect of the present invention comprise an excitation device 4 for directing an energy wave 5 to the contrast agent2 and a detector 7 for acquiring a response signal 6 emitted from the contrast agent 2, e.g. produced by the interaction of the energy wave 5 with the dispersed gas-filled microparticles 3, e.g. microspheres.
  • the system 1 may comprise as an excitation device 4/detector 7 assembly at least one ultrasound transducer, e.g.
  • an ultrasound unit adapted for emitting as an energy wave 5 an ultrasound wave directed at the contrast agent 2 and for subsequently detecting an ultrasonic response signal 6 from the contrast agent 2.
  • Alternative read-out devices may be based on the interaction of contrast agents with electromagnetic ( F) waves.
  • Systems 1 according to embodiments of the first aspect of the present invention may furthermore comprise a control unit 8 adapted for controlling the experimental set-up and parameters of the read-out device (basically amplitude, frequency and/or waveform), and for calculating, based on the response signal 6, a radiation dose received by the contrast agent 2, hence by the previously irradiated body or a portion thereof.
  • This radiation dose may comprise any known radiation-related quantity as known to a person skilled in the art, such as, as discussed hereabove, absorbed dose in mass, Kerma, equivalent dose, effective dose and/or operational dose quantities.
  • the amount of radiation, e.g. radiation dose, used in radiation therapy is measured in gray (Gy), and varies depending on the type and stage of cancer being treated.
  • the typical dose for a solid epithelial tumor ranges from 60 to 80 Gy, while lymphoma tumors are treated with 20 to 40 Gy.
  • Preventative (adjuvant) doses are typically around 45 - 60 Gy in 1.8 - 2 Gy fractions (for Breast, Head and Neck cancers respectively).
  • radiation oncologists can be considered by radiation oncologists when selecting a dose, including, but not limited thereto, whether the patient is receiving chemotherapy, whether radiation therapy is being administered before or after surgery, and the degree of success of surgery.
  • the control unit may refer to any device or portion of a device that processes electronic data, e.g. from registers and/or memory, to transform that electronic data into other electronic data that may for example be stored in registers and/or memory.
  • a control unit may include one or more processors.
  • Such control unit 8 may comprise a computer system, a dedicated integrated programmable unit or may be provided in an integrated system for collecting data from response signals obtained after excitation of a contrast agent 2 by an energy wave 5, e.g. by means of an ultrasound or electromagnetic transmission/reception unit.
  • the control unit 8 may furthermore be adapted for determining a spatial distribution, e.g. a planar and/or a volumetric distribution, of the previously received radiation dose.
  • control unit 8 it may be advantageous to adapt the contrast agent 2 in order to restrict mobility of the dispersed microparticles 3, e.g. by using a contrast agent in a gel emulsion, or by using a targeted contrast agent, e.g. in liquid state, in which the microparticles 3 may chemically bond with a target having structural integrity, e.g. specific membrane receptors in a biological cellular matrix.
  • Calculating the radiation dose may comprise application, e.g. fitting, of a predetermined model characterizing the dose-dependence of quantities related to the response signal 6 for the microparticles 3, e.g. microspheres, comprised in the contrast agent 2.
  • Calculating the radiation dose may furthermore comprise compensating for time- dependent factors relating to interaction of the contrast agent 2 with the energy wave 5 or with the surrounding medium.
  • the contrast agent 2 may be adapted for introduction into a biological system, e.g. by perfusion and/or diffusion into a plant, animal or human, or in samples obtained therefrom.
  • the contrast agent 2 may furthermore be adapted for in-vivo introduction, e.g. injection into an animal or human subject.
  • Such contrast agent 2 may for example be injected into a patient for noninvasive in-situ radiation dose monitoring, e.g. during radiotherapy.
  • the actual step of in-vivo introduction of the contrast agent 2 does not form part of the present invention.
  • FIG. 2 An exemplary embodiment of the system 1 is illustrated by the schematic shown in FIG. 2. It comprises an experimental set-up based on an ultrasonic read-out device, capable of sending and acquiring ultrasonic signals at a wide range of amplitudes and frequencies, and of analyzing the response signals in terms of phase velocity dispersion, attenuation dispersion, and nonlinearity dispersion. The results of this read-out system are used in the examples provided herebelow.
  • this exemplary embodiment comprises a sample of liquid 20, for example placed in a holder 21, e.g. a 2cmx2cmx4cm glass holder.
  • the sample of liquid 20 may be a contrast agent 2 solution comprising microparticles 3, e.g. microspheres or gas-filled micro-bubbles, such as known ultrasound contrast agents, but may also be replaced by a reference sample of pure water or saline solution, e.g. for calibration. Since a few decades now, microscopic bubbles or micro-bubbles are used in contrast agents for ultrasound imaging. These microbubbles may have a substantially spherical shape and may for example be composed of a gas core encapsulated by a lipid monolayer membrane shell.
  • the gas can be any gas, as long as it is not toxic for biological systems, e.g. air or nitrogen.
  • the gas may be a heavier gas, such as perfluorocarbon, in order to avoid diffusion of the gas through the shell, thereby improving the micro-bubble stability.
  • the gas may be a mixture of gasses, e.g. argon and methane, in order to obtain a strong response between ionizing radiation and the gas.
  • Ultrasound contrast agents comprising encapsulated gas-filled microbubbles have been known and used by skilled persons in the art since as early as 1990, for instance as disclosed in US5,236,693. However, the use of such contrast agents for non-invasive in-situ dosimetry has not been found in any of the prior art documents.
  • dosimetry of such contrast agents can improve safety and optimize the treatment efficiency when using ionizing radiation on tumors.
  • This need has been addressed by the applicant by proving the existence of some influence of ionizing radiation on the encapsulated gas-filled microbubbles and, in addition, to a point where this influence is measureable and quantifiable acoustically or electromagnetically.
  • a dose-dependent response of micro-bubbles 3 when exposed to ionizing radiation is described.
  • Those examples verify the change of properties of the bubbles 3 under the influence of ionizing radiation by evaluating the alteration of physico-chemical properties, e.g. the ultrasonic characteristics, of the microbubble solution.
  • Such a correlation between the change in physico-chemical properties, e.g. ultrasonic response, of the bubbles 3 and the dose imparted to the bubbles 3 may be used in other embodiments of the present invention as an non-invasive in-situ dosimetry system, e.g. for determining radiation dose at a particular location, e.g. the location of a tumor in the body of a patient.
  • the encapsulated microbubbles behave very similarly to red blood cells (erythrocytes) and when applied in vivo or in situ the encapsulated microbubbles according to embodiments of the present invention dissolve after a time in the order of minutes, depending on the type of encapsulated microbubbles used.
  • the encapsulated microbubbles of the present invention comprise a safe bio-profile, e.g. a low toxicity as disclosed by Juffermans et al. in Neth Heart J. 2009 February, 17 (2): 82-86.
  • the sample of liquid 20 is contained in the holder 21 and may be continuously stirred by a stirrer 22, for example a magnetic stirrer, in order to prevent microbubbles 3 from floating to the surface or sticking to the bottom of the holder 21.
  • the holder 21 may feature an opening 23, 24 on two sides, for example two opposite sides of the holder 21, so that an excitation device 4, e.g. in the form of an emitting transducer, and a detector 7, e.g. in the form of a receiving transducer, may be placed in operational contact with the liquid 20.
  • the distance between emitter and detector may range from 1 to 2 cm.
  • These emitting and receiving transducers 4, 7 may operate at a suitable operation frequency, e.g.
  • the operating part of the excitation device 4 and the detector 7, i.e. the part being in operational contact with the liquid 20, may have any suitable dimensions, for example a diameter in a range between 0.3 cm to 5 cm. In the examples below, measurements were carried out using 10 MHz, 0.5" (1.3 cm) diameter transducers 4 for emission, and 10 MHz, 0.25" (0.6 cm) diameter transducers 7 for detection.
  • An energy wave 5, for example in the form of an ultrasonic or RF signal, directed by the emitting transducer 4 to the contrast agent 2, may be produced with a waveform generator 25 coupled to the emitting transducer 4, for example a waveform generator 25 controlled by a software interface, e.g. implemented in LabVIEW.
  • Such generated ultrasonic or RF signals may comprise consecutive sinusoidal bursts with frequencies in a pre- determined frequency range, ranging for example from 0.5 MHz (starting frequency) to 20 MHz (ending frequency), at a pre-determined step frequency, e.g. with 250 kHz steps, and with a predetermined number of multiplier cycles, e.g. between 8 to 50 cycles.
  • the burst signal may be sent either directly to the emitting transducer 4 or fed into an intermediate amplifier linked to the emitting transducer 4.
  • the need for an amplifier may be determined on the basis of the nonlinearity parameter reading, as would be clear to a person skilled in the art.
  • the receiving transducer 7, for example mounted with respect to the holder 21 diametrically opposite to the emitting transducer 4, may for example be coupled to a data acquisition card (DAQ) 26 in a computer.
  • This DAQ 26 may record a time signal, for example measuring a pre-determined time period, e.g. 30-200 microseconds in length, with a pre-determined sampling rate, e.g.
  • the received signals may furthermore be processed by taking a pre-determined number of averages, e.g. 16, 32, 64, 128 or 250 averages, and may be stored in a memory, for example a memory forming part of a computer 27, for further analysis.
  • a pre-determined number of averages e.g. 16, 32, 64, 128 or 250 averages
  • the present invention relates to a method for measuring radiation dose.
  • a contrast agent 2 comprising dispersed gas-filled microspheres 3 is exposed to ionizing radiation, for example, a contrast agent 2 as discussed hereabove in the context of the first aspect of the present invention.
  • This exposing to ionizing radiation may comprise exposure to natural radiation present in the environment, e.g. originating from cosmic radiation and natural radioactive isotopes, for example present in soil, atmosphere and/or building materials.
  • this exposing to ionizing radiation may comprise an exposure to a source for characterizing said source, e.g. for quantifying a radioisotope preparation.
  • this exposing to ionizing radiation may also comprise introducing the contrast agent 2 in a sample for quantifying and/or monitoring of radiation exposure of such sample under controlled or uncontrolled exposure conditions.
  • This exposing to ionizing radiation may particularly comprise injection of the contrast agent 2 into a complex system, e.g. a biological system, such as an animal or human body, to quantify and/or monitor the dose distribution of radiation internally or externally administered to such complex system.
  • exposing the contrast agent 2 to ionizing radiation may comprise injecting the contrast agent 2 into a human or animal patient and administering radiation to said patient, in order to characterize a dose-related quantity expressing radiation exposure to said patient or to at least one volume of interest in the patient's body.
  • the method according to the second aspect of the present invention comprises directing an energy wave 5 to the previously exposed contrast agent 2, and acquiring a response signal 6 from the contrast agent 2.
  • contrast agents may be developed with a high dedicated sensitivity to ionizing irradiation.
  • the energy wave 5 may be adapted to the contrast agent used, for optimizing read-out characteristics related to the response signal 6, e.g. for optimizing the magnitude of the response signal.
  • the contrast agent 2 is considered to be an ultrasound contrast agent
  • the energy wave 5 is an ultrasonic energy wave suitable for inducing a strong response signal for detection, e.g. comprising reflections of the ultrasonic wave on material interfaces in the contrast agent 2.
  • the energy wave may be an electromagnetic (F) wave, for example a radiofrequency wave suitable for inducing a strong response signal from a contrast agent 2 adapted for such radiofrequency waves.
  • F electromagnetic
  • contrast agent properties and energy wave characteristics should be adapted to each other, in view of high responsiveness to irradiation and high read-out sensitivity.
  • the method according to embodiments of the present invention furthermore comprises determining the radiation dose received by the contrast agent 2 during the preceding ionizing radiation exposure, taking into account the detected response signal 6.
  • this determining of the radiation dose may take into account an ultrasonic response of ultrasound contrast agent micro-bubbles 3, e.g. ultrasonic properties such as phase velocity, attenuation and/or nonlinearity dispersion, and a predetermined dose-dependent characterization of such ultrasonic properties.
  • determining of the radiation dose may take into account an electromagnetic, e.g. RF, response of contrast agent micro-bubbles 3.
  • Determining of the radiation dose may furthermore comprise determining a spatial distribution, e.g. a planar and/or a volumetric distribution, of the radiation dose.
  • a spatial distribution based on voxel responses can be achieved using a 2D ultrasound probe (phased array).
  • the time dependent backscattered signals at individual voxels can be analyzed and compiled to obtain a full 3D image.
  • Each line of the ultrasound array can correspond to a 2D image (planar images) and the different planar images together generate a full (3D) image.
  • a 3D ultrasound image can be achieved by using a 2Darray of transducer elements in contact with the object to be scanned.
  • ID transducer arrays may be used to produce e.g. 2D B-scan images at known locations in 3D space.
  • Alternative embodiments of image acquisition can involve sweeping a ID transducer array through a known trajectory using a mechanical device.
  • Other embodiments of image acquisition strategies can comprise letting a clinician sweep a ID transducer array manually across the subject and using for instance some sort of tracking device to measure its trajectory.
  • 3D ultrasound advantageously contributes to eliminating operator dependence in the scanning process.
  • 3D data enable 3D visualization techniques such as volume rendering and surface rendering to be employed as disclosed by Prager et al. in Proc. IMechE Vol. 224 Part H: J. Engineering in Medicine.
  • Determining the radiation dose may for example comprise determining the radiation dose received by a patient during administering of radiation, taking into account the detected response signal 6.
  • the determining of the radiation dose may be implemented in a control unit, e.g. a computer, for example the control unit 8 according to embodiments of the first aspect of the present invention.
  • a control unit e.g. a computer
  • the present invention relates to the use of a contrast agent 2 comprising dispersed microparticles 3, e.g. microspheres, for example a contrast agent comprising gas-filled micro-bubbles, for non-invasive in-situ dosimetry.
  • a contrast agent 2 comprising dispersed microparticles 3, e.g. microspheres, for example a contrast agent comprising gas-filled micro-bubbles, for non-invasive in-situ dosimetry.
  • the invention relates to a computer program product for, if implemented on a control unit 8, performing a method, e.g. controlling and performing a measurement, according to embodiments of the second aspect of the invention.
  • the present invention relates to a data carrier storing a computer program product according to embodiments of the fourth aspect.
  • the present invention relates to transmission of a computer program product according to embodiments of the fifth aspect over a transmission medium such as a local or wide area network.
  • a transmission medium such as a local or wide area network.
  • Such micro-bubbles may for example be suitable for functionalization by state-of-the-art techniques in order to be able to specifically target particular cells, e.g. cancer cells, allowing thus radiation dose quantification at a tumor site.
  • cancer cells after functionalization, may induce a permanent change in the micro-bubbles.
  • This change can be detected using different physical principles and/or probes, depending on the chosen bubbles design, e.g. by state-of-the-art ultrasound or electromagnetic imaging in the case of gas-filled micro-bubble ultrasound contrast agents (UCA).
  • UCA gas-filled micro-bubble ultrasound contrast agents
  • Ultrasound contrast agents or targeted molecular agents can be used for therapy.
  • targeted molecular agents lower the energy threshold for cavitation.
  • microbubbles cavitate they preferably concentrate the ultrasound energy within a certain region. This region can be selected by for instance steering and focusing an energy beam, e.g. an ultrasound beam.
  • Targeted molecular imaging agents e.g. ultrasound agents, used in embodiments of the present invention, can be used as beacons to detect regions of disease and then to concentrate an energy wave, e.g. ultrasound energy, within the target region.
  • Contrast enhanced ultrasound for instance has applications for e.g. treatment of thrombosis and drug delivery.
  • a drug or a pharmacon can be incorporated into the encapsulated microbubbles or into encapsulated micro- and nanobubbles according to embodiments of the invention.
  • nanoparticles which may be adapted to be injected in a tumor before radiotherapy, can also be incorporated or loaded into the encapsulated micro- and/or nanobubbles according to embodiments of the invention.
  • An example of such nanoparticles are for instance nanoparticles by Nanobiotix.
  • these nanoparticles can locally boost and/or enhance the radiation dose given to the tumor. This incorporation or loading can be done by a variety of different methods.
  • Target drug delivery with these micro and/or nanobubbles is preferably most useful for highly active drugs or pharmacons that preferably do not require large payloads of the drug for biological effect.
  • Many chemotherapeutics, proteins, gene-based drugs or pharmacons are sufficiently active for delivery when applying an energy wave, for instance ultrasound, an d targeted acoustically or electromagnetically active carriers.
  • an energy wave for instance ultrasound, an d targeted acoustically or electromagnetically active carriers.
  • the presence of the gas in for instance a gene-filled micro- or nanobubbles allows ultrasound energy to burst them.
  • a high energetic wave is preferably generated according to embodiments of the present invention after dosimetry has been performed, as for dosimetry the encapsulated gas-filled microparticles need to be intact.
  • a low intensity, e.g. low pressure, energy wave may preferably be used for performing the dose measurement and, in a next step, after the radiation therapy, a high energy or high pressure wave signal may be generated and applied which is high enough to burst and destroy the bubbles and as a result to release a drug or pharmacon encapsulated in the bubbles.
  • the pressure or energy needed to destroy the bubbles depends on the kind of bubbles. Typically a pressure or energy high than 60kPa may be used, up to 1000 kPa.
  • FIGs. 24(a)-(e) schematically illustrate several embodiments of microbubbles, and how the microbubbles can transport drugs or pharmacons.
  • the stabilizing materials are shown as lipids, but they could be another material, such as polymeric materials.
  • FIG. 24(a) illustrates a drug or pharmacon attached to the membrane surrounding the microbubble.
  • FIG. 24(b) illustrates a drug or pharmacon embedded within the membrane itself.
  • material such as DNA can be bound non-covalently to the surface of the microbubble, as illustrated in FIG. 24(c). Drug and gas can also be loaded into the interior of the microbubble, as shown in FIG. 24(d).
  • FIG. 24(d) schematically illustrate several embodiments of microbubbles, and how the microbubbles can transport drugs or pharmacons.
  • the stabilizing materials are shown as lipids, but they could be another material, such as polymeric materials.
  • FIG. 24(a) illustrates a drug or pharmacon attached to the membrane surrounding
  • hydrophobic drugs can be incorporated into a layer of oily material that forms a film around the microbubble, which is then surrounded by a stabilizing membrane.
  • a targeting ligand is incorporated in the membrane, allowing targeted delivery of the drug.
  • microbubbles and ultrasound techniques used in embodiments of the invention have the potential to being incorporated into other paradigms for molecular images.
  • magnetically responsive materials can also be incorporated into microbubbles for M I.
  • Hybrid forms of imaging incorporating magnetic and optical properties with microbubbles may be exploited to increase sensitivity and therapeutic potential.
  • Such hybrid imaging techniques may improve sensitivity for molecular imaging and our ability to characterize disease.
  • the effects of ionizing radiation on a bubbly liquid, i.e. a contrast agent 2 comprising micro-bubbles 3 have not, to the inventors' knowledge, been previously studied. The insight that there is an effect of ionizing radiation on a bubbly liquid, lies at the basis of the present invention.
  • an ultrasound contrast agent namely lipid or protein shells and gas
  • UCA ultrasound contrast agent
  • the process of lipid peroxidation is a free radical reaction that occurs with unsaturated lipids.
  • the reason for the fact that the lipids need to be unsaturated lies in the presence of a large number of reactive allyl sites. At these sites a reaction can be initiated by abstraction of a hydrogen atom, starting a chain reaction of free radical reactions.
  • the first step in this cascade is the further reaction of the allyl radical with oxygen forming a hydroperoxide.
  • This hydroperoxide can in turn be oxidized further or act as an oxidizing agent itself. It is now possible that cross-linking reactions between different lipid molecules, such as e.g. phospholipids, take place. Many peroxide bindings can create a firm polymer network.
  • Ionizing radiation can provide the initialization of this process.
  • lipid peroxidation occurs in the lipids, e.g. phospholipids, in the shell of a microbubble 3 of a UCA 2
  • the polymerization of the hydrocarbon chains may result in a change of the different properties of the shell.
  • the permeability of the layer may be influenced by an increase in the dielectric constant and by increasing microviscosity.
  • a decrease in the shell thickness is a possible consequence of the oxidation.
  • the top illustration (a) in FIG. 3 shows a schematic representation of the polymerization of the phospholipids of an encapsulated microbubble 3.
  • the polymerization is represented as bars 30 between the different phospholipids 31 that are represented by a hydrophilic head 32 and by two hydrocarbon tails 33.
  • Phospholipids 31 are sensitive to hydrolysis of the ester bonds that are present. During this process fatty acids 34 are released from the phospholipid 31. The remaining part of the molecule has now become a lyso-phospholipid 35 with only one tail 33 left. In the absence of radiation the process can take place both in an acid and in a base environment. The only requirement is the presence of water. In a base environment, the hydrolysis works according to an addition-elimination mechanism. Here a nucleophile hydroxide-ion is added to the carbonyl group, creating a transit state. This addition step is followed by an elimination of the fatty acid 34. The formed carboxylic acid will undergo an acid-base reaction where the equilibrium is towards the right of the reaction.
  • Ionizing radiation could again start up the hydrolysis reaction by splitting water into radicals including a hydroxide radical.
  • the phospholipids are part of the encapsulating shell 37 of a microbubble 3 of an UCA2, they will change the equilibrium radius of curvature. This can be understood by revisiting the stability conditions for micelles.
  • the type of micelle that may be formed is mainly determined by the molecular structure of the micelle components (usually surfactants, such a phospholipids).
  • surfactants such a phospholipids
  • the ionizing radiation can interact with the content gas 36.
  • the formation of radicals here, can again affect the encapsulated molecules.
  • Another possible mechanism may influence the core content 36 of the bubble 3.
  • Ionizing radiation can cause the addition reaction of different gas components: A + B ⁇ AB . This change in gas content may inspire volume changes. Such volume changes must of course be followed by a change in equilibrium radius.
  • the bottom illustration (c) in FIG. 3 gives an overview of the influence of ionizing radiation on the content gas 36.
  • the proposed models for interaction between ionizing radiation and ultrasound contrast agents 2 may change the physical and chemical properties of the content gas 36 and the encapsulating shell 37, a change in ultrasonic or electromagnetic (RF) behaviour may follow.
  • RF electromagnetic
  • the influence of individual parameter changes on attenuation, phase velocity, non-linearity and/or scattering properties may be evaluated through a parameter study. Concretizing findings thereby obtained to the case of the proposed ionizing radiation - UCA interaction may pose two difficulties.
  • a first problem relates to the complexity of the reactions. This makes it unlikely that only one parameter will be independently affected as opposed to multiple interacting parameters. For example: polymerization is believed to make the shell 37 more stiff. If this is the case, then both the shear modulus G s and the shear viscosity 7J S will be affected.
  • a second obstacle is the employed ultrasonic model itself.
  • Such a model may rely on some simplifying assumptions. It is not unthinkable that the influence of ionizing radiation is so severe that the system of the bubbly liquid 2 arrives at a situation where some of those assumptions no longer hold. This would render the entire model useless for the situation at hand. Furthermore, the amount of available models for describing bubble dynamics in liquids is enormous.
  • the first step was to prove the existence of some influence of ionizing radiation on UCA's 2 to the point where it is measurable acoustically.
  • a next step was to link the experimental results to the theoretical propositions.
  • a commercially available micro-bubble contrast agent 2 MicroMarker ® from Bracco
  • Different vials of the micro-bubble contrast agent 2 were irradiated using two different radiation qualities: X-rays, obtained from an X-ray tube using a 15 mAs exposure of 250 keV at the calibration facility of SCK «CEN Mol, Belgium, and Co-60 gamma rays, having 1.17MeV and 1.33MeV energies, obtained from spent nuclear fuel, at the RITA facility of SCK «CEN Mol, Belgium.
  • X-rays obtained from an X-ray tube using a 15 mAs exposure of 250 keV at the calibration facility of SCK «CEN Mol, Belgium
  • Co-60 gamma rays having 1.17MeV and 1.33MeV energies
  • the dose rate was about lOGy/min. This very high dose rate enabled imparting a very high dose to the bubbles 3, in a relatively short time, therefore limiting the influence of the spontaneously occurring time changes of the micro-bubbles 3, related to diffusion.
  • the temperature of the microbubble contrast agents 2 was monitored during both types of irradiation, and was observed to remain constant. Therefore the observed radiation-induced changes in ultrasonic dispersion properties of the contrast agents may not be related to radiation-induced temperature rise, and may only be attributed to more direct interaction effects, such as discussed hereinabove.
  • FIG. 2 is an illustration of the experimental setup used for the ultrasonic dispersion analysis of UCA enriched solutions.
  • the dispersive characteristics of three parameters were analyzed as a function of the dose: ultrasound wave phase velocity, attenuation and nonlinearity. All results were corrected for diffusion by taking into account the evolution over time of non-irradiated bubbles 3.
  • FIG. 2 is an illustration of the experimental setup used for the ultrasonic dispersion analysis of UCA enriched solutions.
  • the dispersive characteristics of three parameters were analyzed as a function of the dose: ultrasound wave phase velocity, attenuation and nonlinearity. All results were corrected for diffusion by taking into account the evolution over time of non-irradiated bubbles 3.
  • FIG. 4 shows the time evolution of typical dispersion characteristics in the absence of radiation: respectively, from top to bottom, (a) difference between maximal and minimal phase velocity, more specifically a drop in phase velocity jump at resonance in MicroMarker solution (closed vial), (b) maximal attenuation at resonance, more specifically a drop in attenuation in MicroMarker solution (closed vial) and (c) maximum nonlinearity parameter, more specifically a drop in nonlinearity parameter in MicroMarker solution (closed vial). Details of the measurement procedure are explained in the "measurement procedure" section.
  • FIG. 5 shows the results of the typical dispersion characteristics obtained after irradiation of the bubbles 3 for different cumulative dose levels.
  • both the emitting transducer 4 and the receiving transducer 7 were calibrated by means of an ONDA, type HGL0400 (1-20 MHz) hydrophone measuring the output in water at a distance of approximately 2 cm (roughly the same distance between the transducers in the glass holder 21).
  • FIG. 6 shows the resulting graph at lOmV input (before source amplification), more specifically FIG. 6 shows the calibration curve from a 10 MHz transducer. The amplitude is illustrated versus the frequency. With the output of the hydrophone at 0.1V (with pre- amplification) the peak response of the transducer stays below 62.5 kPa.
  • the acquired data resulting from the experimental ultrasonic transmission set-up can be processed in different ways.
  • the received signals 6 were compared to signals originating from known reference liquids, such as pure water.
  • This method relies on a reference that needs to be measured before the actual bubbly liquid can be measured.
  • the advantage of this method can be found in the fact that temperature fluctuations are factored out.
  • the method only uses the first echo, which has the highest amplitude, from each signal.
  • the disadvantages are the caution that must be taken in removing the reference liquid from the sample holder 21 and the fact that the nonlinear parameter can only be calculated from 1-10 MHz with information on the phase velocity and attenuation from 0.5-20 MHz.
  • Such method is also known as an insert-substitution method.
  • Other methods for the determination of phase velocity, attenuation and nonlinearity may include the analysis of multiple echo signals. This method has the advantage that no reference medium is used. The disadvantage however is the fact that the analysis involves unknown reflection coefficients.
  • This Gaussian beam expansion can be used as input for the parabolic approximation resulting in the KZK equation for a nonlinear, dissipative and dispersive medium.
  • the nonlinearity is incorporated in this equation through a term proportional to the nonlinearity parameter ⁇ 2 ; p is the density of the liquid and c 0 its velocity. Solutions to these equations can be constructed with so-called Green's functions. From the linear superposition principle it follows that the fundamental pressure field can also be express as
  • the system can be simplified. First of all it may be assumed that the distance between emitting transducer 4 and receiving transducer 7 is less than 2 cm. Next, the density is considered identical in pure and bubbly liquids. In addition, Isoton II is assumed to be non-attenuating, and the fundamental frequency pressure at the emitter surface is not modified in a bubbly liquid. Finally, diffraction effects are considered to be the same with and without contrast agents.
  • OC is the attenuation coefficient
  • c 0 is the velocity of the reference liquid
  • z the distance from the emitting transducer
  • c the frequency dependent velocity of the bubbly liquid
  • the phase velocity can be determined by a cross-correlation between the first echoes of the signal received for the reference signal and for the bubbly liquid respectively. This will result in a time difference At that can be used to determine the phase velocity as follows z
  • the nonlinear parameter can be directly calculated from the ratio between itself and the nonlinearity parameter of the reference liquid that is given as:
  • the frequency dependent nonlinear parameter for a UCA can be written down as: where it can be noted that in order to obtain the nonlinearity parameter at frequency / , the attenuation needs to be known at frequency 2f .
  • Bubble size distributions can be determined in different ways. The easiest way is to look up the distribution in previous literature studies. For SonoVue, which has already been approved for human use, the size distribution is well documented. For MicroMarker this is not the case and therefore the size distribution needs to be actually measured. The most common practice is to use a Coulter Multisizer or a Coulter Counter. These devices rely on what is known as the Coulter principle. An alternative method is a microscopical investigation. The procedure here is to fix a few microliters of the bubble solution on a microscope glass. The solution is then put under a predetermined magnification, e.g. a 40x or lOOx magnification, and pictures of a predetermined number of different locations, e.g.
  • a predetermined magnification e.g. a 40x or lOOx magnification
  • single measurement comprises the recording of the response signals in the frequency range 0.5-20 MHz in steps of 0.25 MHz.
  • each single measurement allows a determination of the experimental phase velocity, attenuation and nonlinearity dispersion relations.
  • the sample holder 21 is filled with a predetermined amount of a reference liquid such as distilled water (e.g. 15 ml).
  • a reference liquid such as distilled water (e.g. 15 ml).
  • An energy wave 5 is emitted to the sample in the sample holder 21, and a response signal 6 is determined.
  • a single measurement is taken without determination of phase velocity, attenuation or nonlinearity parameter.
  • the sample holder 21 is emptied and filled with a predetermined amount of diluents such as a saline solution, e.g. 0.9% NaCI in distilled water, such as an Isoton II solution, which contains a phosphate buffer, e.g. 15 ml.
  • a saline solution e.g. 0.9% NaCI in distilled water
  • Isoton II solution which contains a phosphate buffer, e.g. 15 ml.
  • a single measurement is taken for the pure saline solution, and the phase velocity, attenuation and nonlinearity dispersion relations are determined by the reference method. Distilled water is taken as reference.
  • a vial of an ultrasonic contrast agent is prepared.
  • MicroMarker Contrast Agent comprising a white powder
  • MicroMarker Contrast Agent comprising a white powder
  • the vial is vented and gently agitated for a predetermined time period, for example 1 minute.
  • the solution needs to rest for a while, for example ten minutes. At this point the concentration of the solution in the example described is 2.10 9 microbubbles/ml.
  • a small amount of ultrasonic contrast agent e.g. MicroMarker solution
  • a predetermined volume e.g. a volume of 30 microliter
  • the predetermined amount e.g. 15 ml
  • diluent e.g. Isoton II
  • the sample holder 21 is emptied and cleaned, e.g. washed with distilled water.
  • the sample holder 21 is refilled with a predetermined amount, e.g. 15 ml, of diluent, e.g. Isoton II.
  • Step 4 and 5 may be repeated twice to ensure repeatability and to be able to take averages.
  • phase velocity, attenuation and nonlinearity measurements were carried out by use of the reference method.
  • values for the phase velocity and nonlinearity parameter can be found in literature.
  • First pure water was used as a reference to a pure saline solution.
  • saline solution without contrast agents is used as a reference to saline solutions with enrichment of contrast agents.
  • Random Interleaved Sampling (RIS) was employed to achieve a 1 GHz effective sampling rate.
  • FIG. 8 shows the result of Isoton II particle phase velocity measurements based on RIS recording of the response signals at 1 GHz. Virtually no dispersion is noticeable. Processing of the raw data to obtain the value of the particle velocity dispersion includes, for each current frequency value, looking for a maximum in the cross-correlation function within a 60 ns interval around the maximum obtained for the previous frequency step, i.e. obtained for one frequency increment below the frequency currently being analyzed. The maximum at the lowest frequency in the analyzed range, e.g. lMHz is just the absolute maximum of the cross- correlation function.
  • FIG. 9 shows the calculated phase velocity dispersion for a MicroMarker solution, e.g. a contrast agent, containing 4million bubbles/ml at two different input amplitudes: 10 mV (graph 91) and 50 mV (graph 92).
  • the figure is in good agreement with theory in that the predicted jump in phase velocity at resonance is clearly visible.
  • the figure also shows the influence of pressure on the bubble solution. It can be clearly seen that at pressures well above 60 kPa the shift at the resonance frequency becomes less pronounced and less steep indicating that the size distribution of the microbubbles has become wider. The resonance frequency also appears to have shifted towards a higher frequency indicating that the larger bubbles are being destroyed more rapidly. This is again in agreement with theory.
  • FIG. 10 shows a measurement of the phase velocity dispersion for SonoVue contrast solution with a volume fraction of 4x10 s .
  • the low resonance frequency makes detection of the entire transition difficult in the range 0.5-20 MHz with 10 MHz emitting transducers 4 and receiving transducers 7.
  • FIG. 11 shows an example of Isoton II attenuation dispersion with a distilled water reference. The graph clearly shows a typical form that is somewhat deviating from the expected behaviour in that it shows negative attenuation and in that it is not flat. However, compared to the high attenuation that microbubbles create, this anomaly is no cause for concern.
  • FIG. 13 shows the result of a measurement regarding attenuation on a SonoVue solution with a volume fraction of 4x10 s .
  • a clear peak can be identified at the resonance frequency of 2.25 MHz. This is, however, not always the case.
  • the level of nonlinearity of the liquid solution is the most difficult parameter to process. Not only does it rely on an accurate determination of the second harmonic signal, but also on correct information on the previously determined variables, namely the phase velocity and attenuation. Furthermore, the choice of window function appears to be important as is illustrated in FIG. 14(b) which illustrates the dependence of nonlinearity dispersion on window function. In most cases the Blackman-Nuttall window seems to produce the smoothest curves. It is however worth noting that all windows do indicate a large rise in the nonlinearity parameter dispersion in the lower frequency range, consistent with theory.
  • the nonlinear parameter of the Isoton II reference as determined by measuring relative to water, can be used to help with the final window choice. Good measurements keep the nonlinearity parameter of Isoton II nearly constant at 3.5-3.6 (FIG. 14 (a)).
  • FIG.15 shows the nonlinearity parameter dispersion for a MicroMarker solution
  • the resonance frequency is around 5.5 MHz.
  • the peak in nonlinearity is situated at 1.75 MHz. This is considerably lower than half the resonance frequency.
  • the figure also shows a secondary smaller peak at frequencies higher than the resonance frequency.
  • a curve for the nonlinearity parameter of a SonoVue solution with a volume fraction of 4x10 s is given in FIG. 16. This graph is less smooth than the graph for MicroMarker. This can be related to the more difficult measurements of the phase velocity and attenuation.
  • the nonlinearity parameter is influenced by the presence of bubbles 3, as it shows very high values at frequencies half the resonance frequency or lower.
  • FIG. 17 shows the influence of concentration of MikroMarker microbubbles (illustrated as #/ml in FIG.
  • phase velocity dispersion and attenuation dispersion The concentrations used for the graphs range from 2 to 8 million bubbles/ml.
  • the phase velocity and attenuation dispersion seem to scale linearly with concentration. In terms of the typical dispersion characteristics, a doubling concentration results in a phase velocity jump at resonance that is twice as large and a maximal attenuation that is twice as high. Another observation is the gradual shift in resonance frequency, when comparing different concentrations.
  • FIG. 18 pictures the resonance frequency as a function of the microbubble concentration (illustrated in 10 s #bubbles/ml) and thus illustrates the influence of microbubble concentration on the resonance frequency.
  • a linear rise in the frequency is noticeable. However, the rise is fairly small (from 4 MHz to 5 MHz for a factor four increase in bubble concentration), especially when compared to the step size (0.25 MHz). Looking back at simulations from theory, there is indeed a prediction of a comparable shift in resonance frequency with increased concentration of bubbles.
  • the dashed line illustrates a linear fit through the data points.
  • FIG. 19 shows the influence of concentration on the linear parameters: phase velocity dispersion and attenuation dispersion. More specifically FIG. 19 (a) shows the phase velocity for different concentrations of SonoVue contrast solutions, whereas FIG. 19 (b) illustrates attenuation for difference concentrations of SonoVue contrast solutions.
  • the concentrations of SonoVue contrast solutions used for the graphs range from 2xl0 "5 volume fraction to 8 xl0 "5 volume fraction, indicated as ⁇ on the graphs.
  • the results are similar to those for MicroMarker solutions (compare FIG. 17).
  • the different properties again seem to scale quite good with concentration. Again a linear rise in resonance frequency can be distinguished and this is represented in FIG.
  • lOGy/min in the BR2
  • a step by step guide to ensure reproducible results of experiments on ultrasonic contrast agents aimed at understanding the possible influence of ionizing radiation is presented here.
  • a single measurement comprises the recording of the response signals in the frequency range 0.5-20 MHz in steps of 0.25 MHz.
  • each single measurement allows a determination of the experimental phase velocity, attenuation and nonlinearity dispersion relations.
  • a somewhat adapted measurement sequence is required:
  • the sample holder 21 is filled with a predetermined amount of a reference liquid such as distilled water (e.g. 15 ml).
  • a reference liquid such as distilled water (e.g. 15 ml).
  • An energy wave 5 is emitted to the sample in the sample holder 21, and a response signal 6 is determined.
  • a single measurement is taken without determination of phase velocity, attenuation or nonlinearity parameter.
  • the sample holder 21 is emptied and filled with a predetermined amount of diluents such as a saline solution, e.g. Isoton II (0.9% NaCI in distilled water) solution, which contains a phosphate buffer, e.g. 15 ml.
  • a saline solution e.g. Isoton II (0.9% NaCI in distilled water
  • a phosphate buffer e.g. 15 ml.
  • a single measurement is taken for the pure saline solution and the phase velocity, attenuation and nonlinearity are determined by the reference method. Distilled water is taken as reference.
  • a vial of an ultrasonic contrast agent is prepared.
  • MicroMarker Contrast Agent comprising a white powder
  • MicroMarker Contrast Agent comprising a white powder
  • the vial is vented and gently agitated for a predetermined time period, for example 1 minute.
  • the solution needs to rest for a while, for example ten minutes. At this point the concentration of the solution in the example described is 2.10 9 microbubbles/ml.
  • a small amount of ultrasonic contrast agent e.g. MicroMarker solution
  • a predetermined volume e.g. a volume of 30 microliter
  • the predetermined amount e.g.15 ml of diluents, e.g. Isoton II
  • the sample holder 21 is emptied and cleaned, e.g. washed with distilled water.
  • the sample holder 21 is refilled with a predetermined amount, e.g. 15 ml, of diluent, e.g. Isoton II. 6.
  • Step 4 and 5 may be repeated twice to ensure repeatability and to be able to take averages.
  • the reconstituted vial of ultrasonic contrast agent e.g. of MicroMarker
  • ionizing radiation e.g. of MicroMarker
  • Step 7 and 8 are repeated for the desired concentration yielding information on the influence of different doses on the ultrasonic properties of the microbubbles.
  • the dose which is the amount of radiation that the sample actually receives, expressed in Gray (Gy).
  • the dose rate is a measure of the rate at which the radiation is delivered to the sample. Both of these aspects were investigated.
  • the jump in phase velocity at resonance the evolution of the maximal attenuation at resonance, the maximal nonlinear parameter and the possible shift in resonance frequency.
  • FIG. 5(a) shows the time-corrected results that were obtained for different vials and normalized to the reference measurements at 0 Gy. In the presented figure a clear dependence of the jump in the phase velocity at resonance to the administered dose can be noticed.
  • FIG. 5(b) gives an overview of the maximal attenuation measurements that were conducted on four different vials.
  • the maximal attenuation value is normalized to the reference at 0 Gy.
  • Low dose rate measurements, of 0.7 Gy/min, (circles and squares show rather good linear relationships between dose and maximal attenuation.
  • experiments conducted on two different vials at B 2 with high dose rates, of 10 Gy/min, (triangle and diamond) also are showing a clear linear relationship.
  • FIG. 5(c) shows the results of the analysis of the dose dependence of the maximal nonlinearity parameter. A clear influence on the ionizing radiation is again visible. However, this time the results are not pointing towards a linear relationship. The presented measurements indicate a sharp rise for doses up to 20 Gy, followed by a plateau and less steep rise for higher doses. Discussion
  • a fit between experiment and theory provides information on the values of the parameters of the theoretical model. This can be done using for example standard Matlab routines such as Isqcurvefit. Due to the high number of parameters the fitting procedure can be tackled in different ways. First the focus will be on retrieving parameters for the size distribution of the ultrasound contrast agent, e.g. the MicroMarker contrast agents.
  • the next step is to transform the interpolated data to a Gaussian mixture model fit, e.g. a sum of 5 Gaussian functions.
  • a parameter fit needs to be carried out to find 15 different parameters, 3 (the centre radius, the width and the relative height) for each Gaussian function.
  • a nonlinear inversion has to be conducted. This may for example be done in Matlab by using the routine Isqcurvefit.
  • the table herebelow shows the 15 parameters that were obtained, while FIG. 22 (illustrating the normalized amplitude in function of the radius) shows the results of the fitting, displaying the five individual Gaussians and their sum which appears to be a very good approximation of the interpolated curve.
  • the ultrasonic dispersion graphs can be fitted using a four parameter fitting procedure with the following parameters: G s - d so ,
  • the graphs can be analyzed as follows.
  • the fits 232, 234, for the attenuation (a) and phase velocity (V) are good, but not perfect.
  • the attenuation suffers from a bad approximation at higher frequencies.
  • the size distribution was determined from an analysis of microscopic images.
  • An inherent problem with the microscopy technique for determining the size distribution is the inability to detect very small bubbles.
  • An underestimation of the small bubbles that have high resonance frequencies could explain this discrepancy.
  • the fit 236 for the nonlinearity parameter ( ⁇ ) dispersion shows the largest deviation from the measured values 235. Again the higher frequencies are underestimated while the extra peak at very low frequencies was not observed in experiments. This may be attributed to the low signal amplitudes (especially for the second harmonic) in the lower frequency range that are a result from the fact that 10 MHz transducers 4, 7 were employed for emission and reception.
  • the encapsulated gas-filled microbubbles are bubbles which can produce an echo for reception and analysis, to afford imaging of a region.
  • phase velocity, attenuation and nonlinearity Increasing doses resulted in an increasing maximal attenuation, an increasing maximal nonlinearity and an increasing magnitude of the jump in the phase velocity.
  • determination of phase velocity, attenuation, and/or nonlinearity dispersion characteristics of microbubbles 3 in contrast agents 2 may be used for determining radiation dose.

Abstract

L'invention concerne la dosimétrie de rayonnement in situ non invasive. Un système (1) pour mesurer une dose de rayonnement comprend un dispositif d'excitation (4) conçu pour diriger une onde d'énergie (5) au niveau d'un volume d'une substance comprenant des microparticules remplies de gaz (3), un détecteur (7) pour détecter un signal de réponse (6) émis et/ou modifié à partir du volume de la substance (2) comprenant des microparticules remplies de gaz (3), et une unité de commande (8). L'unité de commande (8) est conçue pour calculer une dose de rayonnement ionisant précédemment reçu par le volume de la substance (2) sur la base du signal de réponse (6). L'invention concerne également un procédé pour mesurer une dose reçue de rayonnement ionisant et l'utilisation de l'agent de contraste (2) pour une dosimétrie in situ non invasive.
PCT/EP2012/067539 2011-09-07 2012-09-07 Dosimétrie de rayonnement in situ non invasive WO2013034709A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US14/343,112 US9035268B2 (en) 2011-09-07 2012-09-07 Non-invasive in-situ radiation dosimetry
EP12756201.5A EP2758130B1 (fr) 2011-09-07 2012-09-07 Dosimétrie de rayonnement in situ non invasive

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
GBGB1115419.2A GB201115419D0 (en) 2011-09-07 2011-09-07 Non-invasive in-situ radiation dosimetry
GB1115419.2 2011-09-07

Publications (1)

Publication Number Publication Date
WO2013034709A1 true WO2013034709A1 (fr) 2013-03-14

Family

ID=44882315

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2012/067539 WO2013034709A1 (fr) 2011-09-07 2012-09-07 Dosimétrie de rayonnement in situ non invasive

Country Status (4)

Country Link
US (1) US9035268B2 (fr)
EP (1) EP2758130B1 (fr)
GB (1) GB201115419D0 (fr)
WO (1) WO2013034709A1 (fr)

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2015107179A1 (fr) * 2014-01-19 2015-07-23 Dosevue Nv Applicateur très peu invasif pour dosimétrie de rayonnement in situ
WO2015124499A1 (fr) * 2014-02-18 2015-08-27 Dosevue Nv Écarteur d'organe dosimétrique localement injectable
US9649079B1 (en) 2014-10-09 2017-05-16 General Electric Company System and method to illustrate a radiation dose applied to different anatomical stages of an exposed subject
WO2019002947A1 (fr) * 2017-06-29 2019-01-03 Insighten, Ltd. Fréquence ultrasonore et optimisation de la taille des microbulles dans un traitement par ultrasons assisté par microbulles
CN112763519A (zh) * 2020-12-22 2021-05-07 清华大学 一种用拟蒙特卡罗方法模拟光子散射的方法
EP3675956A4 (fr) * 2017-08-31 2021-10-13 Mayo Foundation for Medical Education and Research Système et procédé de thérapie par particules de carbone pour le traitement d'arythmies cardiaques et d'autres maladies
US11358007B2 (en) 2017-06-29 2022-06-14 Insighten, Ltd. Ultrasound frequency and microbubble size optimization in microbubble-enhanced ultrasound treatment

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR102342210B1 (ko) * 2014-11-26 2021-12-28 삼성전자주식회사 프로브, 초음파 영상 장치 및 초음파 영상 장치의 제어 방법
DE102016108022A1 (de) * 2016-04-29 2017-11-02 Claudia Resch Bilderzeugungsvorrichtung zur ortsauflösenden Vermessung von Änderungen der Dichte in 3-dimensionalen dielektrischen Objekten
US11369810B2 (en) * 2016-12-19 2022-06-28 Michalakis Averkiou Method and apparatus for ultrasonic mediation of drug delivery using microbubbles
WO2018213809A1 (fr) * 2017-05-19 2018-11-22 Sarah Kathryn Patch Thérapie par particules assistée par microbulles et ultrasons
CN108478936B (zh) * 2018-02-28 2019-10-01 武汉大学 通过质子诱导热声信号确定质子治疗剂量与范围的方法及设备
CN109521457B (zh) * 2018-09-25 2022-10-21 中国辐射防护研究院 一种基于信息准则的γ辐射源项划分方法及系统
CN113804709B (zh) * 2021-09-22 2022-08-12 清华大学 基于拟蒙特卡罗和强制探测的校正ct散射信号的方法

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5236693A (en) 1990-11-14 1993-08-17 Brigham And Women's Hospital Medical ultrasound contrast agent and method of using same
US20040236207A1 (en) 2001-11-30 2004-11-25 Widener Steven R. Single-use external dosimeters for use in radiation therapies and related methods, systems and computer program products
WO2010073164A1 (fr) * 2008-12-23 2010-07-01 Koninklijke Philips Electronics, N.V. Système d'imagerie acoustique et procédé d'imagerie acoustique avec quantification de contraste
US20110081724A1 (en) * 2009-10-06 2011-04-07 Massachusetts Institute Of Technology Method and apparatus for determining radiation

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4309307A (en) * 1979-01-22 1982-01-05 The United States Of America As Represented By The United States Department Of Energy Gas mixtures for gas-filled radiation detectors
US20110040171A1 (en) * 2003-12-16 2011-02-17 University Of Washington Image guided high intensity focused ultrasound treatment of nerves
US20070213616A1 (en) * 2005-10-20 2007-09-13 Thomas Anderson Systems and methods for arteriotomy localization

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5236693A (en) 1990-11-14 1993-08-17 Brigham And Women's Hospital Medical ultrasound contrast agent and method of using same
US20040236207A1 (en) 2001-11-30 2004-11-25 Widener Steven R. Single-use external dosimeters for use in radiation therapies and related methods, systems and computer program products
US20110121188A1 (en) 2001-11-30 2011-05-26 Black Robert D Single-use internal dosimeters for detecting radiation in medical procedures/therapies
WO2010073164A1 (fr) * 2008-12-23 2010-07-01 Koninklijke Philips Electronics, N.V. Système d'imagerie acoustique et procédé d'imagerie acoustique avec quantification de contraste
US20110081724A1 (en) * 2009-10-06 2011-04-07 Massachusetts Institute Of Technology Method and apparatus for determining radiation

Non-Patent Citations (4)

* Cited by examiner, † Cited by third party
Title
JUFFERMANS ET AL., NETH HEART J., vol. 17, no. 2, February 2009 (2009-02-01), pages 82 - 86
L. HOFF: "Ph.D. thesis", 2000, NORWEGIAN UNIVERSITY OF SCIENCE AND TECHNOLOGY, article "Acoustic characterization of contrast agents for medical ultrasound imaging"
NEENU ET AL., NANO REVIEWS, vol. 1, 2010, pages 5358
PRAGER ET AL.: "Proc. IMechE", J. ENGINEERING IN MEDICINE, vol. 224

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2015107179A1 (fr) * 2014-01-19 2015-07-23 Dosevue Nv Applicateur très peu invasif pour dosimétrie de rayonnement in situ
US10188876B2 (en) 2014-02-18 2019-01-29 Dosevue Nv Locally injectable dosimetric organ spacer
WO2015124499A1 (fr) * 2014-02-18 2015-08-27 Dosevue Nv Écarteur d'organe dosimétrique localement injectable
US20170056689A1 (en) * 2014-02-18 2017-03-02 Dosevue Nv Locally Injectable Dosimetric Organ Spacer
US9649079B1 (en) 2014-10-09 2017-05-16 General Electric Company System and method to illustrate a radiation dose applied to different anatomical stages of an exposed subject
CN111132732A (zh) * 2017-06-29 2020-05-08 医视特有限公司 微泡增强超声治疗中的超声频率和微泡尺寸的优化
WO2019002947A1 (fr) * 2017-06-29 2019-01-03 Insighten, Ltd. Fréquence ultrasonore et optimisation de la taille des microbulles dans un traitement par ultrasons assisté par microbulles
CN111132732B (zh) * 2017-06-29 2021-09-21 医视特有限公司 增强对靶组织的治疗同时限制对非靶组织的损伤的系统
US11358007B2 (en) 2017-06-29 2022-06-14 Insighten, Ltd. Ultrasound frequency and microbubble size optimization in microbubble-enhanced ultrasound treatment
US11857807B2 (en) 2017-06-29 2024-01-02 Insightec, Ltd. Simulation-based drug treatment planning
US11938343B2 (en) 2017-06-29 2024-03-26 Insightec, Ltd. Cavitation-enhanced targeted drug delivery and dosing
EP3675956A4 (fr) * 2017-08-31 2021-10-13 Mayo Foundation for Medical Education and Research Système et procédé de thérapie par particules de carbone pour le traitement d'arythmies cardiaques et d'autres maladies
US11857808B2 (en) 2017-08-31 2024-01-02 Mayo Foundation For Medical Education And Research System and method for carbon particle therapy for treatment of cardiac arrhythmias and other diseases
CN112763519A (zh) * 2020-12-22 2021-05-07 清华大学 一种用拟蒙特卡罗方法模拟光子散射的方法
CN112763519B (zh) * 2020-12-22 2022-03-01 清华大学 一种用拟蒙特卡罗方法模拟光子散射的方法

Also Published As

Publication number Publication date
US20140213841A1 (en) 2014-07-31
EP2758130A1 (fr) 2014-07-30
GB201115419D0 (en) 2011-10-19
US9035268B2 (en) 2015-05-19
EP2758130B1 (fr) 2018-05-23

Similar Documents

Publication Publication Date Title
US9035268B2 (en) Non-invasive in-situ radiation dosimetry
US6797257B2 (en) Paramagnetic polymerized protein microspheres and methods of preparation thereof
US9789339B2 (en) System design and method for verifying 3D dosimetric imaging of charged particles in media
CN102834068B (zh) 超声波诊断治疗装置
Gessner et al. Acoustic angiography: a new imaging modality for assessing microvasculature architecture
OˈReilly et al. A super‐resolution ultrasound method for brain vascular mapping
Arvanitis et al. Controlled ultrasound-induced blood-brain barrier disruption using passive acoustic emissions monitoring
Choi et al. Non-invasive and real-time passive acoustic mapping of ultrasound-mediated drug delivery
JP5123183B2 (ja) 標的療法のための画像ベースの計画方法及び装置
Sassaroli et al. Cavitation threshold of microbubbles in gel tunnels by focused ultrasound
Radhakrishnan et al. Relationship between cavitation and loss of echogenicity from ultrasound contrast agents
JP5805651B2 (ja) 標的ナノ粒子及びその磁性粒子を使用する癌等の細胞及び他の生物学的物質の検出、測定、及び撮像
CarsonPaul et al. Dual-modality X-ray-induced radiation acoustic and ultrasound imaging for real-time monitoring of radiotherapy
Vlad et al. An increase in cellular size variance contributes to the increase in ultrasound backscatter during cell death
Tu et al. Intravascular inertial cavitation activity detection and quantification in vivo with Optison
Kamimura et al. Chirp-and random-based coded ultrasonic excitation for localized blood-brain barrier opening
Stapleton et al. Acoustic and kinetic behaviour of definity in mice exposed to high frequency ultrasound
Hughes et al. Perfluorocarbon nanoparticles for molecular imaging and targeted therapeutics
Pellow Nonlinear nanobubble behaviour for vascular and extravascular applications
GB2522240A (en) Minimally invasive applicator for in-situ radiation dosimetry
Huber et al. Ultrasound-Mediated Cavitation of Magnetic Nanoparticles for Drug Delivery Applications
Lei Developments and Applications of Laser-Based and X-Ray-Based Biomedical Thermoacoustic Imaging Techniques
Kasoji Early Assessment of Tumor Response to Radiation Therapy Using High-resolution Contrast Enhanced Ultrasound Imaging Techniques and Applications for Prostate Cancer
Vince Using ultrasound to enhance targeted radiotherapy
Tu Fundamental aspects of ultrasound contrast agent dynamic behaviors and inertial cavitation quantification

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 12756201

Country of ref document: EP

Kind code of ref document: A1

WWE Wipo information: entry into national phase

Ref document number: 14343112

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: DE